CA2385850A1 - Sensor for measuring tissue perfusion - Google Patents
Sensor for measuring tissue perfusion Download PDFInfo
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- CA2385850A1 CA2385850A1 CA002385850A CA2385850A CA2385850A1 CA 2385850 A1 CA2385850 A1 CA 2385850A1 CA 002385850 A CA002385850 A CA 002385850A CA 2385850 A CA2385850 A CA 2385850A CA 2385850 A1 CA2385850 A1 CA 2385850A1
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- Prior art keywords
- tracer
- reservoir
- tissue
- detection cavity
- perfusion
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
- G01F1/704—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow using marked regions or existing inhomogeneities within the fluid stream, e.g. statistically occurring variations in a fluid parameter
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/026—Measuring blood flow
- A61B5/0275—Measuring blood flow using tracers, e.g. dye dilution
Abstract
The invention relates to a method and a sensor for measurement of tissue perfusion. The sensor is provided with a reservoir (4) for a fluid or gaseous tracer and a tracer-permeable barrier (3), a sub-surface of which is in contact with the surrounding tissue and another sub-surface of which is in contact with a detection cavity (5) which is connected to a suitable apparatus for the measurement of tracer concentration in the detection cavity. The concentration of the tracer in the detection cavity is a measure of perfusion in the surrounding tissue. According to another embodiment of the invention it is also possible to carry out measurements of perfusion in the surface layers of the skin or of an organ.
Description
CA 02385850 2002-03-27 pCT~~9/00$22 SENSOR FOR MEASURING TISSUE PERFUSION
TECHNICAL FIELD OF THE INVENTION
The present invention relates generally to methods and devices for measurements of tissue perfusion according to the preamble of independent claims 1 and 7 and more particularly to a method and a sensor for measurement of tissue perfusion over a given variable region and having a short response time.
BACKGROUND ART
Tissue perfusion is a measure of the amount (volume) of blood passing through a unit quantity of the tissue and is often measured with the unit ml blood/100 g tissue.
Since all blood tissue are at the same time being supplied with nutrients and excrete waste products through diffusion between tissue cells and the blood, tissue perfusion is a very important factor indicating the state of health of a tissue. A
method for the measurement of tissue perfusion is therefore highly pertinent, for instance for monitoring tissue during and after surgical operations and transplantations. Monitoring of potentially threatened tissue, e.g. muscular tissue, whose blood supply may become adversely affected by increasing pressure in the connective tissue membrane of the muscle, would be highly pertinent as an indication of when a pressure relieving operation should be initiated.
Likewise monitoring of internal perfusion caused by the formation of oedemas in a heart stopped during operation could provide valuable information about the need of external supply of nutrients to the tissue of the heart. Within medical research, perfusion is an important parameter too.
A number of methods for determination of tissue perfusion are known. A
technique consisting of an injection into the relevant tissue of radioactive xenon as a tracer and measuring the decay of radioactivity as a function of time has been described (see Larsen et al., 1966. Blood Flow through Human Adipose Tissue Determined with Radioactive Xenon. Acta physiol. scand. 66, pp 337-345), but this technique suffers from a number of drawbacks in that its temporal resolution only amounts to approximately half an hour which is insufficient in many situations.
Furthermore the location of the injection of the radioactive matter into the tissue relative to the location where the radioactivity is being measured is not particularly well-defined and finally, the application of radioactive matter per se involves potential hazards.
Another method of measuring tissue perfusion utilises continuous injection of ethanol during microdialysis. During microdialysis a fluid is being pumped very slowly through a fibre inserted into the tissue of the patient. The concentration of the fluid is in equilibrium with the surrounding tissue as the catheter is diffusion-open and the fluid is being collected via a return fibre. This method also suffers from an insufficient temporal resolution.
TECHNICAL FIELD OF THE INVENTION
The present invention relates generally to methods and devices for measurements of tissue perfusion according to the preamble of independent claims 1 and 7 and more particularly to a method and a sensor for measurement of tissue perfusion over a given variable region and having a short response time.
BACKGROUND ART
Tissue perfusion is a measure of the amount (volume) of blood passing through a unit quantity of the tissue and is often measured with the unit ml blood/100 g tissue.
Since all blood tissue are at the same time being supplied with nutrients and excrete waste products through diffusion between tissue cells and the blood, tissue perfusion is a very important factor indicating the state of health of a tissue. A
method for the measurement of tissue perfusion is therefore highly pertinent, for instance for monitoring tissue during and after surgical operations and transplantations. Monitoring of potentially threatened tissue, e.g. muscular tissue, whose blood supply may become adversely affected by increasing pressure in the connective tissue membrane of the muscle, would be highly pertinent as an indication of when a pressure relieving operation should be initiated.
Likewise monitoring of internal perfusion caused by the formation of oedemas in a heart stopped during operation could provide valuable information about the need of external supply of nutrients to the tissue of the heart. Within medical research, perfusion is an important parameter too.
A number of methods for determination of tissue perfusion are known. A
technique consisting of an injection into the relevant tissue of radioactive xenon as a tracer and measuring the decay of radioactivity as a function of time has been described (see Larsen et al., 1966. Blood Flow through Human Adipose Tissue Determined with Radioactive Xenon. Acta physiol. scand. 66, pp 337-345), but this technique suffers from a number of drawbacks in that its temporal resolution only amounts to approximately half an hour which is insufficient in many situations.
Furthermore the location of the injection of the radioactive matter into the tissue relative to the location where the radioactivity is being measured is not particularly well-defined and finally, the application of radioactive matter per se involves potential hazards.
Another method of measuring tissue perfusion utilises continuous injection of ethanol during microdialysis. During microdialysis a fluid is being pumped very slowly through a fibre inserted into the tissue of the patient. The concentration of the fluid is in equilibrium with the surrounding tissue as the catheter is diffusion-open and the fluid is being collected via a return fibre. This method also suffers from an insufficient temporal resolution.
3 discloses a method and a microsensor which is able to measure tissue perfusion, but measurements are limited to a very narrow space, and any heterogeneities of the tissue will thus make measurements of average perfusion more complicated.
In connection with monitoring tissue perfusion for instance during surgical operations, the above-mentioned prior art suffers from the drawbacks of either insufficient temporal resolution or a very limited measurement space.
DISCLOSURE OF THE INVENTION
In order to circumvent the drawbacks and limitations of methods and devices for the measurement of tissue perfusion of prior art as mentioned above, it is the object of the present invention to provide a method and a device (sensor) for the measurement of tissue perfusion which is able to integrate measurements of tissue perfusion over a larger region in the tissue, the dimensions of which region can be varied as desired.
It is a further object of the present invention to provide a method and a device with a response time not exceeding a few minutes.
It is a further object of the present invention to provide at least one embodiment of the general inventive idea which makes it possible to carry out non-invasive measurements of skin perfusion or measurements of prefusion in the surface layers of an organ, for instance for assessment of insufficient blood circulation.
These objects are accomplished with a method according to the characterising clause of claim 1 and a device (sensor) according to the characterising clause of claim 7.
Various advantageous embodiments of the invention are defined in the dependent claims.
In the method and sensor for tissue perfusion according to the invention a fluid or gaseous tracer from a suitable supply means is supplied to a reservoir in which a constant high concentration of the tracer is maintained through diffusion from the supply means and from which reservoir a small portion of the tracer molecules will diffuse into a tracer-permeable barrier which is partly in contact with the surrounding tissue. From this barrier, part of the tracer molecules will move out into the surrounding tissue via a first spatially extended area, whereas another portion of the tracer molecules will move into an adjoining detector cavity via a second spatially extended area, said detector cavity being in communication with a suitable detector apparatus measuring the concentration of tracer in the detection cavity. The movement of tracer molecules from the reservoir into the surrounding tissue thus takes place via a tracer-permeable barrier which is in contact with the surrounding tissue via said first spatially extended area and the portion of the tracer molecules moving into the detection cavity arrives at the detection cavity via a tracer-permeable barrier and said second spatially extended area. Said first area thus constitutes the area of contact between said tracer-permeable barrier and the surrounding tissue, whose perfusion is to be measured, whereas said second area constitutes the area through which tracer molecules are able to reach the detection cavity. The distribution between the diffusion to the surrounding tissue and the diffusion to the detection cavity will be determined by the flow of dissolved matter in the surrounding tissue, i.e. the perfusion, such that if the transport in the tissue is of large magnitude only a small portion of the tracer will diffuse into the detection cavity and vice versa. The signal from the detection apparatus will thus become a measure of tissue perfusion in the region surrounding the fibre.
According to the present invention the dimensions of the contact region between said tracer-permeable barrier and the surrounding tissue can be varied and thereby the region over which the tissue perfusion measurement is being carried out.
It is also possible to vary the second area providing access to the detection cavity. By varying the geometry of the sensor, i.e. the relative layout of the reservoir, barrier and detection cavity, it is possible to vary the sensitivity and the radial resolution of the measurements being performed. It is furthermore possible to utilise a mixture of at least two tracers which might be supplied and removed substantially momentarily. A time-based measurement after instantaneous supply/removal to/from the tracer reservoir of two tracers with different diffusion coefficients will make it possible to distinguish between how much of the diffusion of the tracers away from the tracer reservoir is due to the concentration gradient within the tissue and how much is due to the transportation of the tracers away from the tissue by the blood. Thus, independent measures of perfusion and of diffusion coefficients within the tissue can be obtained.
According to the invention it is furthermore possible to carry out measurements of OZ and C02 and other gasses present in the tissue simultaneously with tissue perfusion.
As a suitable tracer for tissue perfusion measurements for instance helium, argon or hydrogen could be used, but it would also be possible to use other tracers.
Finally for in-situ calibration purposes the patient can inhale a gas which is being detected by the sensor placed in the tissue.
BRIEF DESCRIPTION OF THE DRAWINGS
The invention will now be described by way of exemplifying embodiments hereof and with reference to the accompanying drawings in which 5 Figure 1 a is a longitudinal section of a first embodiment of a sensor according to the present invention;
Figure 1 b is a cross section along the line indicated by A-A in Figure 1 a;
Figure 2a is a longitudinal section of a second embodiment of a sensor according to the present invention;
Figure 2b is a cross section along the line indicated by B-B in Figure 2a;
Figure 3a is a side elevation cross-sectional view of a first version of a fourth embodiment of the present invention;
Figure 3b is a side elevation cross-sectional view of a second version of a fourth embodiment of the present invention;
Figure 4a is a side elevation cross-sectional view of a first version of a fifth embodiment of the present invention comprising interlaced reservoir- and detection cavity sections;
Figure 4b is a side elevation cross-sectional view of a second version of a fifth embodiment of the present invention comprising interlaced reservoir- and detection cavity sections;
Figure 5 is the response of a microsensor according to the invention as a function of time for a sudden change of perfusion obtained in a specific experiment; and Figure 6 is a calibration curve of the sensor, i.e. the signal from the sensor as a function of the velocity of water obtained in the same experiment as mentioned in connection with Figure 5.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
In the following detailed part of the present description a number of different embodiments of the present invention will be described with reference to the accompanying drawings, but it is understood that these embodiments only constitute examples of the general inventive idea, and that other embodiments may be conceivable by a person skilled in the art.
The first embodiment of the sensor is shown in Figure 1 a and Figure 1 b. The sensor is substantially symmetrical about a vertical plane 11 and comprises two U-shaped profiles 1, 2, the reservoir profile 1 and the detection profile 2 made of a gas-impermeable material such as metal or a suitable plastic material. The open sides 12, 13 of these two profiles 1, 2 are both in sealing abutment with a barrier disposed between the reservoir 4 and the detection cavity 5 and extending throughout the vertical length of the sensor. The barrier 3 is made from a gas-permeable material, such as silicon or Teflon, such that two cavities, the reservoir 4 and the detection cavity 5, are defined. At the distal end hereof both the reservoir 4 and the detection cavity 5 are closed by a gas-impermeable barrier 6. At its proximal end the reservoir 4 is provided with an open inlet 7 which via a tube (not shown) is in communication with a supply container (also not shown) containing a gaseous tracer (for instance helium). The outer walls of both the tube and the container are made from a gas-impermeable material. The detection cavity 5 is at its proximal end provided with an open outlet 8 which via a tube (not shown) is in communication with a detector apparatus (vacuum pump and mass spectrometer as it is well-known within the art). The tube between the outlet 8 and the detector apparatus is made from a gas-impermeable and pressure resistant material. The reservoir profile 4, the detection cavity profile 5 and the barriers 3, 6 will in the following be referred to as the fibre.
The fibre is designed to be positioned within the tissue of a patient whose perfusion in that part of the tissue is to be measured. The functional principle of the invention is that a constantly high concentration of the tracer is maintained in the reservoir 4, the concentration being maintained via diffusion from the supply container. A
small portion of the molecules of the tracer will due to diffusion move from the reservoir 4 out into the gas-permeable barrier 3 and a portion hereof will move out into the surrounding tissue through a first area 18, as indicated by the arrows 9, while another portion will move into the detection cavity 5 through a second area 13, as indicated by the arrows 10, and eventually be detected by means of the detection apparatus. The distribution between the diffusion to the surrounding tissue and the diffusion to the detection cavity 5 will be determined by the transport of dissolved matter in the surrounding tissue, such that if the transport in the tissue is of a large magnitude only a small portion of the tracer will diffuse into the detection cavity 5 and vice versa. The signal from the detection apparatus will thus become a measure of tissue perfusion in the region surrounding the fibre.
Figure 2a and Figure 2b show a second embodiment of the present invention.
Throughout the following description of the second embodiment of the present invention, elements identical with elements of the first embodiment shown in Figure 1 a and Figure 1 b will be designated by the same reference numerals as on Figure 1 a and Figure 1 b. The second embodiment is also substantially symmetrical about a vertical plane 11 and comprises two tubes: the reservoir tube 14 defining the reservoir 4 and the detection tube 15 defining the detection cavity 5, both tubes being made from a semi-gas-impermeable material (plastics). These two tubes 14, 15 are separated from each other by a barrier 19 made from a gas-impermeable material, such as metal or plastics. At the distal end, both the reservoir 4 and the detection cavity 5 are closed by a gas-impermeable barrier 6. At its proximal end the reservoir tube 14 is provided with an open inlet 7 which via a tube with gas-impermeable wall (not shown) is in communication with a supply container constructed from a gas-impermeable material containing a gaseous tracer (for instance helium). The detection tube 5 is at its proximal end provided with an outlet 8 communicating via a pressure resistant tube with gas-impermeable wall with a detection apparatus (vacuum pump and mass spectrometer as it is well-known within the art). The reservoir tube 14, the detection tube 15 and the barriers 6, 19 will in the following be referred to as the fibre.
The fibre is designed to be positioned within the tissue of a patient whose perfusion in that part of the tissue is to be measured. The functional principle of the invention is that a constantly high concentration of the tracer is maintained in the reservoir 4, the concentration being maintained via diffusion from the supply container. A
small portion of the molecules of the tracer will due to diffusion move from the reservoir 4 out through the wall of the reservoir tube 14 through a first area 14' (as delimited by the two arrows C in Figure 2b) and into the surrounding tissue, as indicated by the arrows 9. Of this quantity of tracer, a portion will diffuse into the detection tube and pass through the wall (15) through a second area 15' (as delimited by the two arrows D in Figure 2b) to the detection cavity 5 as indicated by the arrows 16, from where it will be detected by the detection apparatus. The quantity reaching the detection cavity will depend on the transport conditions in the tissue through which diffusion takes place, and the signal from the detector will thus be a measure of the transport conditions, i.e. the perfusion, in the region around the fibre.
A third embodiment (not shown) of the present invention is directly derivable from the two first embodiments described above in that the structures shown in Figure 1 and Figure 2 are helically wound around the longitudinal axis 11 of the fibres. This has the effect of making the sensitivity of the fibres in a plane perpendicular to the longitudinal axis omnidirectional. A suitable pitch of the helix could for instance constitute 10 revolutions per cm.
Figure 3a and 3b show a fourth embodiment of the present invention which differs significantly from the three previous embodiments described above. Where the three above embodiments were designed to be inserted into the tissue, the fourth embodiment of the present invention is fastened non-invasively on the surface (20) of the skin or of an organ of a patient to provide the possibility of carrying out measurements of perfusion in the surface layers of the skin or the organ such as carried out for the assessment of insufficient blood circulation in for instance a leg of the patient.
The operational principle of the first version of the fourth embodiment shown in Figure 3a corresponds to the operational principle of the first embodiment shown in Figure 1 a and Figure 1 b. The operational principle of the second version of the fourth embodiment shown in Figure 3b corresponds to the operational principle of the second embodiment shown in Figure 2a and Figure 2b.
In the embodiment shown in Figure 3a, the inner side, i.e. the side facing the surface (20) of the skin or organ of the patient, of a gas-impermeable disc 17 is provided with a single one of the sensors according to the first embodiment of the present invention shown in Figure 1 a and Figure 1 b. The longitudinal axis 11 of the sensor extends substantially parallel with the plane of said disc 17 and one of the sides 18 of the tracer-permeable barrier 3 is in contact with the surface (20) of the patient's skin or organ. Diffusion of tracer molecules from the barrier 3 into the skin or organ thus only takes place via this single side 18. The function of the disc 17 is to enable sufficient contact pressure between fibre and skin or organ and to prevent escape of tracer molecules in the direction opposite the skin or organ.
In the embodiment shown in Figure 3b the inner side, i.e. the side facing the surface (20) of the skin or organ of the patient, of a gas-impermeable disc 17 is provided with a single one of the sensors according to the second embodiment of the present invention shown in Figure 2a and Figure 2b. The longitudinal axis 11 of the sensor extends substantially parallel with the plane of said disc 17 and parts of the tracer-permeable walls 14 and 15 of the reservoir 4 and detection cavity 5, respectively, are in contact with the surface of the patient's skin or organ. The width w of the tracer-impermeable barrier is modified compared to the second embodiment in order to provide a contact area of sufficient size between the reservoir 4 and the surface of the skin or organ and between the detection cavity 5 and the skin or organ, respectively. Also the side of the reservoir 4 facing away from the detection cavity 5 and the side of the detection cavity 5 facing away from the reservoir 4 are covered with tracer-impermeable barriers 19.
A more preferable variation of the embodiments shown in Figure 3a and Figure 3b is shown in Figure 4a and Figure 4b. The difference between the embodiments shown in Figures 3a/3b and Figures 4a/4b is that both the reservoir 4 and the detection cavity 5 in the embodiments shown in Figure 4a and Figure 4b are split up into a plurality of substantially identical reservoir/detection cavity sub-systems covering a substantial part of the inner side of said gas-impermeable disc 17.
The functional principles of the embodiments shown in Figure 4a and Figure 4b correspond to those described in connection with the preceding embodiments and will hence not be described in detail here.
In the embodiments of the present invention according to Figures 3a, 3b, 4a and 4b it is possible to provide the inner side of the disc 17 with a system of partially open channels where the openings are in contact with the surface 20 of the patient's skin or organ, and where the channels can be connected to a suitable vacuum source.
Application of vacuum to the channels ensures a firm attachment of the disc 17 to 5 the skin or organ of the patient.
Figure 5 shows the response of the sensor in volts as a function of time obtained in an experiment where water moves through a sand-filled tube simulating a bloodflow through tissue. The velocity of the water changed suddenly from 4.8 10 micrometers/second to the left of the arrow in the Figure to 24.8 micrometers/second immediately to the right of the arrow. A response time of approximately 0.5 - 1.0 minutes is possible, although the response time varies as a function of perfusion, and increases when the velocity through the tissue changes from a relatively high level to a relatively low level and vice versa.
Figure 6 shows a calibration curve obtained in the same experiment as in Figure 5, i.e. a curve of the signal from the detection device in Volts as a function of the velocity of water in mm/second.
Above, a number of different embodiments of the present invention have been shown and described, but it is understood that these embodiments only constitute examples of the general inventive idea as defined in the accompanying claims, and that other embodiments of the present invention might be conceivable by a person skilled in the art.
In connection with monitoring tissue perfusion for instance during surgical operations, the above-mentioned prior art suffers from the drawbacks of either insufficient temporal resolution or a very limited measurement space.
DISCLOSURE OF THE INVENTION
In order to circumvent the drawbacks and limitations of methods and devices for the measurement of tissue perfusion of prior art as mentioned above, it is the object of the present invention to provide a method and a device (sensor) for the measurement of tissue perfusion which is able to integrate measurements of tissue perfusion over a larger region in the tissue, the dimensions of which region can be varied as desired.
It is a further object of the present invention to provide a method and a device with a response time not exceeding a few minutes.
It is a further object of the present invention to provide at least one embodiment of the general inventive idea which makes it possible to carry out non-invasive measurements of skin perfusion or measurements of prefusion in the surface layers of an organ, for instance for assessment of insufficient blood circulation.
These objects are accomplished with a method according to the characterising clause of claim 1 and a device (sensor) according to the characterising clause of claim 7.
Various advantageous embodiments of the invention are defined in the dependent claims.
In the method and sensor for tissue perfusion according to the invention a fluid or gaseous tracer from a suitable supply means is supplied to a reservoir in which a constant high concentration of the tracer is maintained through diffusion from the supply means and from which reservoir a small portion of the tracer molecules will diffuse into a tracer-permeable barrier which is partly in contact with the surrounding tissue. From this barrier, part of the tracer molecules will move out into the surrounding tissue via a first spatially extended area, whereas another portion of the tracer molecules will move into an adjoining detector cavity via a second spatially extended area, said detector cavity being in communication with a suitable detector apparatus measuring the concentration of tracer in the detection cavity. The movement of tracer molecules from the reservoir into the surrounding tissue thus takes place via a tracer-permeable barrier which is in contact with the surrounding tissue via said first spatially extended area and the portion of the tracer molecules moving into the detection cavity arrives at the detection cavity via a tracer-permeable barrier and said second spatially extended area. Said first area thus constitutes the area of contact between said tracer-permeable barrier and the surrounding tissue, whose perfusion is to be measured, whereas said second area constitutes the area through which tracer molecules are able to reach the detection cavity. The distribution between the diffusion to the surrounding tissue and the diffusion to the detection cavity will be determined by the flow of dissolved matter in the surrounding tissue, i.e. the perfusion, such that if the transport in the tissue is of large magnitude only a small portion of the tracer will diffuse into the detection cavity and vice versa. The signal from the detection apparatus will thus become a measure of tissue perfusion in the region surrounding the fibre.
According to the present invention the dimensions of the contact region between said tracer-permeable barrier and the surrounding tissue can be varied and thereby the region over which the tissue perfusion measurement is being carried out.
It is also possible to vary the second area providing access to the detection cavity. By varying the geometry of the sensor, i.e. the relative layout of the reservoir, barrier and detection cavity, it is possible to vary the sensitivity and the radial resolution of the measurements being performed. It is furthermore possible to utilise a mixture of at least two tracers which might be supplied and removed substantially momentarily. A time-based measurement after instantaneous supply/removal to/from the tracer reservoir of two tracers with different diffusion coefficients will make it possible to distinguish between how much of the diffusion of the tracers away from the tracer reservoir is due to the concentration gradient within the tissue and how much is due to the transportation of the tracers away from the tissue by the blood. Thus, independent measures of perfusion and of diffusion coefficients within the tissue can be obtained.
According to the invention it is furthermore possible to carry out measurements of OZ and C02 and other gasses present in the tissue simultaneously with tissue perfusion.
As a suitable tracer for tissue perfusion measurements for instance helium, argon or hydrogen could be used, but it would also be possible to use other tracers.
Finally for in-situ calibration purposes the patient can inhale a gas which is being detected by the sensor placed in the tissue.
BRIEF DESCRIPTION OF THE DRAWINGS
The invention will now be described by way of exemplifying embodiments hereof and with reference to the accompanying drawings in which 5 Figure 1 a is a longitudinal section of a first embodiment of a sensor according to the present invention;
Figure 1 b is a cross section along the line indicated by A-A in Figure 1 a;
Figure 2a is a longitudinal section of a second embodiment of a sensor according to the present invention;
Figure 2b is a cross section along the line indicated by B-B in Figure 2a;
Figure 3a is a side elevation cross-sectional view of a first version of a fourth embodiment of the present invention;
Figure 3b is a side elevation cross-sectional view of a second version of a fourth embodiment of the present invention;
Figure 4a is a side elevation cross-sectional view of a first version of a fifth embodiment of the present invention comprising interlaced reservoir- and detection cavity sections;
Figure 4b is a side elevation cross-sectional view of a second version of a fifth embodiment of the present invention comprising interlaced reservoir- and detection cavity sections;
Figure 5 is the response of a microsensor according to the invention as a function of time for a sudden change of perfusion obtained in a specific experiment; and Figure 6 is a calibration curve of the sensor, i.e. the signal from the sensor as a function of the velocity of water obtained in the same experiment as mentioned in connection with Figure 5.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
In the following detailed part of the present description a number of different embodiments of the present invention will be described with reference to the accompanying drawings, but it is understood that these embodiments only constitute examples of the general inventive idea, and that other embodiments may be conceivable by a person skilled in the art.
The first embodiment of the sensor is shown in Figure 1 a and Figure 1 b. The sensor is substantially symmetrical about a vertical plane 11 and comprises two U-shaped profiles 1, 2, the reservoir profile 1 and the detection profile 2 made of a gas-impermeable material such as metal or a suitable plastic material. The open sides 12, 13 of these two profiles 1, 2 are both in sealing abutment with a barrier disposed between the reservoir 4 and the detection cavity 5 and extending throughout the vertical length of the sensor. The barrier 3 is made from a gas-permeable material, such as silicon or Teflon, such that two cavities, the reservoir 4 and the detection cavity 5, are defined. At the distal end hereof both the reservoir 4 and the detection cavity 5 are closed by a gas-impermeable barrier 6. At its proximal end the reservoir 4 is provided with an open inlet 7 which via a tube (not shown) is in communication with a supply container (also not shown) containing a gaseous tracer (for instance helium). The outer walls of both the tube and the container are made from a gas-impermeable material. The detection cavity 5 is at its proximal end provided with an open outlet 8 which via a tube (not shown) is in communication with a detector apparatus (vacuum pump and mass spectrometer as it is well-known within the art). The tube between the outlet 8 and the detector apparatus is made from a gas-impermeable and pressure resistant material. The reservoir profile 4, the detection cavity profile 5 and the barriers 3, 6 will in the following be referred to as the fibre.
The fibre is designed to be positioned within the tissue of a patient whose perfusion in that part of the tissue is to be measured. The functional principle of the invention is that a constantly high concentration of the tracer is maintained in the reservoir 4, the concentration being maintained via diffusion from the supply container. A
small portion of the molecules of the tracer will due to diffusion move from the reservoir 4 out into the gas-permeable barrier 3 and a portion hereof will move out into the surrounding tissue through a first area 18, as indicated by the arrows 9, while another portion will move into the detection cavity 5 through a second area 13, as indicated by the arrows 10, and eventually be detected by means of the detection apparatus. The distribution between the diffusion to the surrounding tissue and the diffusion to the detection cavity 5 will be determined by the transport of dissolved matter in the surrounding tissue, such that if the transport in the tissue is of a large magnitude only a small portion of the tracer will diffuse into the detection cavity 5 and vice versa. The signal from the detection apparatus will thus become a measure of tissue perfusion in the region surrounding the fibre.
Figure 2a and Figure 2b show a second embodiment of the present invention.
Throughout the following description of the second embodiment of the present invention, elements identical with elements of the first embodiment shown in Figure 1 a and Figure 1 b will be designated by the same reference numerals as on Figure 1 a and Figure 1 b. The second embodiment is also substantially symmetrical about a vertical plane 11 and comprises two tubes: the reservoir tube 14 defining the reservoir 4 and the detection tube 15 defining the detection cavity 5, both tubes being made from a semi-gas-impermeable material (plastics). These two tubes 14, 15 are separated from each other by a barrier 19 made from a gas-impermeable material, such as metal or plastics. At the distal end, both the reservoir 4 and the detection cavity 5 are closed by a gas-impermeable barrier 6. At its proximal end the reservoir tube 14 is provided with an open inlet 7 which via a tube with gas-impermeable wall (not shown) is in communication with a supply container constructed from a gas-impermeable material containing a gaseous tracer (for instance helium). The detection tube 5 is at its proximal end provided with an outlet 8 communicating via a pressure resistant tube with gas-impermeable wall with a detection apparatus (vacuum pump and mass spectrometer as it is well-known within the art). The reservoir tube 14, the detection tube 15 and the barriers 6, 19 will in the following be referred to as the fibre.
The fibre is designed to be positioned within the tissue of a patient whose perfusion in that part of the tissue is to be measured. The functional principle of the invention is that a constantly high concentration of the tracer is maintained in the reservoir 4, the concentration being maintained via diffusion from the supply container. A
small portion of the molecules of the tracer will due to diffusion move from the reservoir 4 out through the wall of the reservoir tube 14 through a first area 14' (as delimited by the two arrows C in Figure 2b) and into the surrounding tissue, as indicated by the arrows 9. Of this quantity of tracer, a portion will diffuse into the detection tube and pass through the wall (15) through a second area 15' (as delimited by the two arrows D in Figure 2b) to the detection cavity 5 as indicated by the arrows 16, from where it will be detected by the detection apparatus. The quantity reaching the detection cavity will depend on the transport conditions in the tissue through which diffusion takes place, and the signal from the detector will thus be a measure of the transport conditions, i.e. the perfusion, in the region around the fibre.
A third embodiment (not shown) of the present invention is directly derivable from the two first embodiments described above in that the structures shown in Figure 1 and Figure 2 are helically wound around the longitudinal axis 11 of the fibres. This has the effect of making the sensitivity of the fibres in a plane perpendicular to the longitudinal axis omnidirectional. A suitable pitch of the helix could for instance constitute 10 revolutions per cm.
Figure 3a and 3b show a fourth embodiment of the present invention which differs significantly from the three previous embodiments described above. Where the three above embodiments were designed to be inserted into the tissue, the fourth embodiment of the present invention is fastened non-invasively on the surface (20) of the skin or of an organ of a patient to provide the possibility of carrying out measurements of perfusion in the surface layers of the skin or the organ such as carried out for the assessment of insufficient blood circulation in for instance a leg of the patient.
The operational principle of the first version of the fourth embodiment shown in Figure 3a corresponds to the operational principle of the first embodiment shown in Figure 1 a and Figure 1 b. The operational principle of the second version of the fourth embodiment shown in Figure 3b corresponds to the operational principle of the second embodiment shown in Figure 2a and Figure 2b.
In the embodiment shown in Figure 3a, the inner side, i.e. the side facing the surface (20) of the skin or organ of the patient, of a gas-impermeable disc 17 is provided with a single one of the sensors according to the first embodiment of the present invention shown in Figure 1 a and Figure 1 b. The longitudinal axis 11 of the sensor extends substantially parallel with the plane of said disc 17 and one of the sides 18 of the tracer-permeable barrier 3 is in contact with the surface (20) of the patient's skin or organ. Diffusion of tracer molecules from the barrier 3 into the skin or organ thus only takes place via this single side 18. The function of the disc 17 is to enable sufficient contact pressure between fibre and skin or organ and to prevent escape of tracer molecules in the direction opposite the skin or organ.
In the embodiment shown in Figure 3b the inner side, i.e. the side facing the surface (20) of the skin or organ of the patient, of a gas-impermeable disc 17 is provided with a single one of the sensors according to the second embodiment of the present invention shown in Figure 2a and Figure 2b. The longitudinal axis 11 of the sensor extends substantially parallel with the plane of said disc 17 and parts of the tracer-permeable walls 14 and 15 of the reservoir 4 and detection cavity 5, respectively, are in contact with the surface of the patient's skin or organ. The width w of the tracer-impermeable barrier is modified compared to the second embodiment in order to provide a contact area of sufficient size between the reservoir 4 and the surface of the skin or organ and between the detection cavity 5 and the skin or organ, respectively. Also the side of the reservoir 4 facing away from the detection cavity 5 and the side of the detection cavity 5 facing away from the reservoir 4 are covered with tracer-impermeable barriers 19.
A more preferable variation of the embodiments shown in Figure 3a and Figure 3b is shown in Figure 4a and Figure 4b. The difference between the embodiments shown in Figures 3a/3b and Figures 4a/4b is that both the reservoir 4 and the detection cavity 5 in the embodiments shown in Figure 4a and Figure 4b are split up into a plurality of substantially identical reservoir/detection cavity sub-systems covering a substantial part of the inner side of said gas-impermeable disc 17.
The functional principles of the embodiments shown in Figure 4a and Figure 4b correspond to those described in connection with the preceding embodiments and will hence not be described in detail here.
In the embodiments of the present invention according to Figures 3a, 3b, 4a and 4b it is possible to provide the inner side of the disc 17 with a system of partially open channels where the openings are in contact with the surface 20 of the patient's skin or organ, and where the channels can be connected to a suitable vacuum source.
Application of vacuum to the channels ensures a firm attachment of the disc 17 to 5 the skin or organ of the patient.
Figure 5 shows the response of the sensor in volts as a function of time obtained in an experiment where water moves through a sand-filled tube simulating a bloodflow through tissue. The velocity of the water changed suddenly from 4.8 10 micrometers/second to the left of the arrow in the Figure to 24.8 micrometers/second immediately to the right of the arrow. A response time of approximately 0.5 - 1.0 minutes is possible, although the response time varies as a function of perfusion, and increases when the velocity through the tissue changes from a relatively high level to a relatively low level and vice versa.
Figure 6 shows a calibration curve obtained in the same experiment as in Figure 5, i.e. a curve of the signal from the detection device in Volts as a function of the velocity of water in mm/second.
Above, a number of different embodiments of the present invention have been shown and described, but it is understood that these embodiments only constitute examples of the general inventive idea as defined in the accompanying claims, and that other embodiments of the present invention might be conceivable by a person skilled in the art.
Claims (16)
1. Method for the measurement of tissue perfusion where a fluid or gaseous tracer is being supplied from a tracer source via a reservoir (4) to the tissue, the perfusion of which is to be measured and detected by a detection device via a detection cavity (5), characterised in that the supply of tracer from said reservoir (4) to the surrounding tissue takes place via a spatially extended first area;
that a part of the tracer molecules leaving said reservoir (4) diffuses to said detection cavity (5) via a spatially extended second area; and that said tissue perfusion is measured as a spatial average value dependent on the size and shape of said first and second areas with the aid of said detection device determining the amount of tracer diffusing into said detection cavity (5).
that a part of the tracer molecules leaving said reservoir (4) diffuses to said detection cavity (5) via a spatially extended second area; and that said tissue perfusion is measured as a spatial average value dependent on the size and shape of said first and second areas with the aid of said detection device determining the amount of tracer diffusing into said detection cavity (5).
2. Method according to claim 1, characterised in that the size and shape of said spatially extended areas can be varied according to the individual application.
3. Method according to claim 1, characterised in that the response time of said method is less than 1 minute.
4. Method according to claim 1, characterised in that at least two tracers are used.
5. Method according to claim 1, characterised in that the tracer is helium.
6. Method according to claim 1, characterised in that O2 and CO2 are being measured simultaneously with tissue perfusion.
7. Sensor for the measurement of tissue perfusion according to claim 1, where a fluid or gaseous tracer is being supplied from a tracer source via a reservoir (4) to the tissue, the perfusion of which is to be measured, and detected by a detection device via a detection cavity (5), characterised in that said sensor comprises:
- first means such that the supply of tracer from said reservoir (4) to the surrounding tissue takes place via a spatially extended first area (14', 18); and - second means such that a part of the tracer molecules leaving said reservoir (4) can arrive at said detection cavity (5) via a spatially extended second area (13, 15').
- first means such that the supply of tracer from said reservoir (4) to the surrounding tissue takes place via a spatially extended first area (14', 18); and - second means such that a part of the tracer molecules leaving said reservoir (4) can arrive at said detection cavity (5) via a spatially extended second area (13, 15').
8. Sensor according to claim 7, characterised in that said first means comprises a tracer-permeable barrier (3, 14), the dimensions of which can be varied and that said second means comprises a tracer-permeable barrier (3,15), the dimensions of which can be varied, such that said variations of said dimensions results in variations of the size and shape of said spatially extended first and second areas according to the individual application.
9. Sensor according to claim 8, characterised in that said reservoir (4) communicates partly with said surrounding tissue through a spatially extended tracer-permeable barrier (3), having a first surface (18) which forms said first area, and partly with said detection cavity (5) through the same spatially extended tracer-permeable barrier (3), having a second surface (13) which forms said second area.
10. Sensor according to claim 8, characterised in that said reservoir (4) communicates with said surrounding tissue through a spatially extended tracer-permeable barrier (14), a first surface (14') of which forms said first area, and partly with said detection cavity (5) via said tissue and through another spatially extended tracer-permeable barrier (15), a second surface (15') of which forms said second area.
11. Sensor according to claim 8, characterised in that said reservoir (4) and said detection cavity (5) are separated by a barrier (3, 19), and that the reservoir (4), barrier (3, 19) and cavity (5) are built together to form a longitudinal sensor.
12. Sensor according to any of the claims 7 to 10, characterised in that said reservoir (4), said detection cavity (5) and said spatially extended tracer-permeable barriers (3, 14, 15) are helically wound around the longitudinal axis (11) of said sensor.
13. Sensor according to any of the claims 7 to 11, characterised in that said reservoir (4), said detection cavity (5) and said spatially extended tracer-permeable barriers (3, 14, 15) are located between one of the large surfaces of a tracer-impermeable panel or disc (17) and the surface (20) of the skin or organ of a patient, the perfusion of the surface layers of which skin or organ is to be measured, and with said longitudinal axis 11 extending substantially parallel with said large surface of the panel or disc (17), such that said spatially extended tracer-permeable barriers (3, 14, 15) are partly in contact with the surface of the skin or organ, and such that tracer can move from said reservoir (4) into said skin or organ and either from here into said detection cavity (5), or directly from said reservoir (4) into said detection cavity (5).
14. Sensor according to any of the claims 7 to 11, characterised in that a series of said reservoir (4), said detection cavity (5) and said tracer-permeable barriers (3, 14, 15) are placed in side-by-side relationship with each other to cover a larger area of tissue.
15. Sensor according to claim 14, characterised in that said series of reservoirs (4), detection cavities (5) and tracer-permeable barriers (3, 14, 15) are located along one of the large sides of said panel or disc (17), such that they cover a substantial part of said side, and such that parts of said tracer-permeable barriers (3, 14, 15) can be brought into contact with the surface of the skin or organ of the patient.
16. Sensor according to claims 13 or 15, characterised in that said panel or disc (17) on the side facing the surface (20) of the skin or organ is provided with a pattern of partially open channels which can be connected to a vacuum source.
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| PCT/DK1999/000522 WO2001024692A1 (en) | 1999-10-04 | 1999-10-04 | Sensor for measuring tissue perfusion |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2385850A1 true CA2385850A1 (en) | 2001-04-12 |
Family
ID=8157159
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002385850A Abandoned CA2385850A1 (en) | 1999-10-04 | 1999-10-04 | Sensor for measuring tissue perfusion |
Country Status (8)
| Country | Link |
|---|---|
| US (1) | US7215988B1 (en) |
| EP (1) | EP1217944B1 (en) |
| JP (1) | JP2003510153A (en) |
| AT (1) | ATE313293T1 (en) |
| AU (1) | AU5968599A (en) |
| CA (1) | CA2385850A1 (en) |
| DE (1) | DE69929092T2 (en) |
| WO (1) | WO2001024692A1 (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| AU2002367084A1 (en) * | 2001-12-21 | 2003-07-15 | Unisense A/S | Multifibre sensor for measuring perfusion |
| EP2391275B1 (en) * | 2008-12-09 | 2018-04-25 | MD Biomedical AB | Device for microdialysis sampling |
Family Cites Families (8)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| USRE30317E (en) * | 1972-11-15 | 1980-07-01 | Hellige Gmbh | Method and apparatus for determining the perfusion efficiency factor of animal tissue |
| FR2684864A1 (en) | 1991-12-12 | 1993-06-18 | Hemodia | METHOD AND DEVICE FOR MEASURING THE CONCENTRATION OF A SUBSTANCE IN A LIQUID COMPLEX MEDIUM, FOR EXAMPLE BLOOD. |
| US5439003A (en) | 1993-12-16 | 1995-08-08 | Modern Technologies Corp. | Apparatus and method for measuring fluid flow |
| US5672827A (en) | 1995-06-07 | 1997-09-30 | American Air Liquide Inc. | Method for measuring the flow rate of a species contained in an exhaust gas stream of a combustion process |
| US5594179A (en) | 1995-11-06 | 1997-01-14 | Marsh-Mcbirney, Inc. | Tracer type flowmeter and method using two or more injected trace materials |
| WO1997019345A1 (en) * | 1995-11-22 | 1997-05-29 | Unisense Aps | Microsensor and use of such microsensor |
| DK174312B1 (en) * | 1996-06-06 | 2002-12-02 | Ole Pedersen | Method for measuring flow rate and diffusivity, microsensor for use in the method and use of such microsensor |
| GB9713043D0 (en) | 1997-06-21 | 1997-08-27 | Aromascan Plc | Gas sensor |
-
1999
- 1999-10-04 US US10/088,582 patent/US7215988B1/en not_active Expired - Fee Related
- 1999-10-04 JP JP2001527696A patent/JP2003510153A/en active Pending
- 1999-10-04 WO PCT/DK1999/000522 patent/WO2001024692A1/en active IP Right Grant
- 1999-10-04 AT AT99974088T patent/ATE313293T1/en not_active IP Right Cessation
- 1999-10-04 AU AU59685/99A patent/AU5968599A/en not_active Abandoned
- 1999-10-04 CA CA002385850A patent/CA2385850A1/en not_active Abandoned
- 1999-10-04 EP EP99974088A patent/EP1217944B1/en not_active Expired - Lifetime
- 1999-10-04 DE DE69929092T patent/DE69929092T2/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| DE69929092T2 (en) | 2006-07-06 |
| ATE313293T1 (en) | 2006-01-15 |
| JP2003510153A (en) | 2003-03-18 |
| AU5968599A (en) | 2001-05-10 |
| US7215988B1 (en) | 2007-05-08 |
| DE69929092D1 (en) | 2006-01-26 |
| WO2001024692A1 (en) | 2001-04-12 |
| EP1217944A1 (en) | 2002-07-03 |
| EP1217944B1 (en) | 2005-12-21 |
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| EEER | Examination request | ||
| FZDE | Discontinued |